Ion selective electrodes

Abstract: A polymeric material which to form a stable, reproducible interface between the ionic and electronic domains of an ion selective sensor, or an ion selective field effect transistor, or the like is provided. When employed in an ion selective sensor, the polymeric material is advantageously provided over a solid internal reference electrode and an ion selective material is provided thereover. According to one embodiment, the polymeric material of the invention includes less than about 1.63 x 10²¹ immobilized charged sites per gram (less than about 2.72 millaequivalents/gram). According to another embodiment, the polymeric material includes immobilized sites of charge opposite that of mobile ions involved in the redox couple. A preferred polymeric material comprises a copolymer of methacrylamidopropyltrimethylammoniumchloride and methylmethacrylate.

Description: The present invention relates generally to ion selective electrodes, and ion selective sensors, and more specifically to a solid contact material for use in such devices. In many settings, for example the clinical laboratory or the analytical or industrial chemical laboratory, the need for rapid analysis of the concentration of a variety of ionic species or analytes in solution exists. Conventionally, in such analyses, an ion selective electrode is brought into contact with a test solution into which a reference electrode is also immersed. The ion selective electrode and the reference electrode are connected via a voltmeter and a potentiometric determination of the activity of a particular analyte in solution is made. The activity measurement may be correlated to the concentration of the analyte in solution using reference solutions or standard solutions of known concentration. Typically, ion selective electrodes have been fabricated according to the following designs. One conventional design consists of an internal redox couple reference electrode, an ion-selective membrane, and an internal liquid electrolyte contacting the reference electrode and the membrane. The ion selective membrane is advantageously fabricated so as to include therein a particular molecule selectively complexing the ion to be analyzed, and the electrolyte advantageously includes a relatively high concentration of the ion to be analyzed and the anion of the redox couple, for example chloride in a silver/silver chloride reference. The potentiometric determination is based upon the principle that the electromotive force detected by the voltmeter is proportional to the logarithmic concentration of analyte in solution. Standard solutions of known analyte concentrations are typically used and a calibration curve is established in such analyses, and the concentration of analyte in the test sample is determined by comparison with the calibration curve. However, such a system requires maintenance of the electrode in an environment in which the electrode is not permitted to dry out, and is not amenable to electrode significant miniaturization, for example in the fabrication of planar electrodes. Hydrogels, that is, neutral polymeric matrices incorporating salts, have been employed in ion selective electrodes in a manner similar to that of the above-described liquid electrolyte. However, hydrogels tend to swell unacceptably during use. Such swelling may have several detrimental effects, one of which is physical disruption, ultimately rupture, of the overlaying ion selective membrane, and another of which is unstable concentration of the analyte ion within the hydrogel as the swell value changes, resulting in imprecision and inaccuracy in analysis. Another ion selective electrode design involves a reference redox couple, for example a silver/silver chloride electrode, covered with a conventional ion selective membrane, and is known as a "coated wire electrode". Such a design would appear to be amenable to miniaturization and to planar electrode fabrication. However, in an ion analysis system, it is important that junction potentials at material and phase interfaces of the overall voltametric determination circuit be as stable and reproducible as possible, so as to assure precision and accuracy in analysis. Instability in interface junction potential of the ion selective membrane/reference redox couple interface is observed in coated wire electrodes, at which a border between a domain of electronic conductivity and ionic conductivity exists, which border is void of chemical or electronic equilibria thereacross due to the lack of an internal contacting solution. Such a border is known in the art as a "blocked" interface. One method of stabilizing such a junction potential is described in EP-A-0 498 572. Described is a redox couple reference contacted by an ion selective membrane including a fortiophore designed to complex an ionic species of the redox couple. U.S. Patent No. 4,434,249 describes the preparation of ion-transfer membranes and methods of preparing such membranes from acrylic monomers and, particularly, of copolymers of at least two acrylic monomers. Specifically described is a membrane composition having a monomeric component (> 88 mol %) of a non-ionic hydrophobic material such as methyl methacrylate (MMA) and a monomeric component (3-12% mol %) of an acrylic monomer containing ionogenous groups such as methacrylamidopropyltrimethylammonium chloride (MAPTAC). The patent describes an optimum concentration level of the ionogenous monomer for transfer of ions across this bulk material, departures from which will decrease transference. No teaching is made of utilizing the material as an interface between two different conducting domains, for example, electronic and ionic domains. EP-A-0 325 562 describes an ion selective electrode in which an ion exchange resin is incorporated between an electrochemical redox couple and an ion selective membrane, the ion exchange resin being selected so as to have ions counter to those to be analyzed chemically linked to the polymer defining the resin. The publication teaches the use of standard, commercially-available ion exchange resins, for example, Amberlite®, Dowex®, and Nafion®, which typically have a capacity on the order of 4.3 milliequivalents per gram, that is, about 2.5 X 10 21 charged sites per gram of material. While neither aqueous swell values nor adherence characteristics of this approach are documented in the publication, ion exchange resins typically swell unacceptably in such circumstances, even to the point of dissolving, and adherence between an ion exchange resin and an inert substrate is generally thought to be poor. Indeed, adhesion between many polymeric materials incorporating charged groups and other polymeric layers or substrates must often be augmented by an intermediate, inert, mesh-like layer such as, for example, silated polyvinylchloride. Therefore, it remains a challenge in the art to formulate a solid state material to serve as an interface between the electronic and ionic domains of ion selective sensors, such material having a rapidly equilibrating, reproducible swell value below that at which physical disruption of any device in which it is employed occurs, which is easy to prepare and use, and which adheres well to typical substrates and to adjacent layers in devices in which it is employed. Accordingly, it is a general purpose of the present invention to provide a means and method of establishing or maintaining a more stable equilibria between electronic and ionic domains, which equilibria facilitate stable and reproducible junction potentials in electrochemical devices, using a material which is easy to prepare and use, which adheres well to typical substrates and adjacent materials in electrochemical devices in which it is employed, and which has a stable and reproducible swell value. The present invention provides an ion selective sensor comprising an electrically conductive material providing a reference redox couple formed from a metal and a salt thereof, the salt including first and second ions, the first ions being ions of the metal having a first charge and the second ions having a second charge opposite the first charge; and an ion selective material selective for potassium, calcium, hydrogen, sodium, or lithium ions convering an intermediate layer of a polymeric material; characterised in that the polymeric material provided on the said electrically conductive material includes third and fourth ions, the third ions being immobilised on the polymeric material, the fourth ions being mobile and being the same as the second ions. The foregoing and other objects and advantages of the present invention are achieved by providing an ion selective sensor comprising an electrically conductive material providing a reference redox couple, a polymeric material having immobilized charged sites provided on the electrically conductive material, and an ion selective material covering the polymeric material. Preferably, the polymeric material carries less than about 1.63 X 10 21 immobilized charge sites per gram. The ion selective electrode may additionally comprise a substrate onto which the electrically conductive reference electrode material is deposited. The present invention also provides a method of providing a stable and reproducible electrical interface between a solid contact reference providing a redox couple formed from a metal and a salt thereof, the salt including first and second ions, the first ions being ions of the metal having a first charge and the second ions having a second charge opposite the first charge and an ion setective material selective for potassium, calcium, hydrogen, sodium, or lithium ions, of an ion selective sensor characterised in that it comprises contacting both the said solid contact reference and the said ion selective material with a polymeric material including third and fourth ions, the third ions being immobilised on the polymeric material, the fourth ions being mobile and being the same as the second ions. It is another object of the present invention to provide a method of providing a stable and reproducible electrical interface between a solid contact reference providing a redox couple and an ion selective material of an ion selective sensor or the like, comprising contacting both the solid contact reference and the ion selective material with a polymeric material having immobilized charged sites, the polymeric material carrying less than about 1.63 X 10 21 immobilized charged sites per gram. The present invention further provides a method of farming an ion selective sensor comprising the steps of providing an electrically conductive material; creating a redox couple formed from a metal and a salt thereof, the salt including first and second ions. the first ions being ions of the metal having a first charge and the second ions having a second charge opposite the first charge, and including a portion of said electrically conductive mateial, coating the said redox couple with a polymeric material including third and fourth ions, the third ions bein g immobilised on the polymeric material, the fourth ions being mobile and being the same as the second ions, and covering the said polymeric material with an ion selective material selective for potassium, calcium, hydrogen, sodium, or lithium ions, and, optionally, selecting an electrically non-conductive substrate; and depositing the said electrically conductive material onto a portion of the said substrate. The above and other features, objects and advantages of the present invention will be better understood from the following specification when read in conjunction with the accompanying drawings, in which: Fig. 1 is a cross-sectional, schematic view of an ion selective electrode according to the prior art; Fig. 2 is a cross-sectional, schematic view of an ion selective electrode according to one embodiment of the present invention; A prior art coated wire ion selective sensor 10 is illustrated in cross-section in Fig. 1, and includes a substantially planar non-conducting substrate 12, and redox couple 14 fabricated thereon. Redox couple 14 typically comprises a metal 16 such as silver, onto which a salt of the metal 18 such as silver chloride is deposited. Ion selective membrane 20 is electrochemically generated thereover, typically covering redox couple 14 and contacting portions of substrate 12 in areas 13 surrounding redox couple 14 which redox couple 14 does not cover. Membrane 20 typically comprises a polymeric membrane incorporating an ion selective species which imparts ion selectivity to the membrane. Such ion selective species may take the form of, for example, a non-dissociable ion-specific ligand, i.e. an ionophore, or an electrically charged liquid ion-exchanger. Lead 22, typically formed of a conductive material such as the metal which comprises metal 16, may pass through substrate 12 just under metal 16 to make contact therewith, as illustrated in Fig. 1, or may be deposited upon substrate 12 so as to make contact with metal 16. According to the latter arrangement (not illustrated), lead 22 would typically be covered by an electrically insulating material at portions which would otherwise make contact with membrane 20. Both of these arrangements are well-known in the art. The scheme at the right of Fig. 1 represents, approximately, the chemical and electrochemical equilibria associated with ion selective electrode 10. In the scheme of Fig. 1, level I represents electronic contact between reference redox couple 14 and lead 22 of circuitry defining analytical apparatus. Level II represents the electrochemical equilibrium associated with typical reference redox couples, for example, one in which M represents a metal such as silver and MX represents the salt of the metal, X being an ion such as chloride. In level III, P 1 A + represents the association between the material of ion selective membrane 20, P 1 , typically polymeric material including an ionophore, and analyte species analyte A + , a cation according to this exemplary scheme. Level IV represents the analyte medium, typically an aqueous solution containing analyte A + . From the scheme of Fig. 1, it can be seen that equilibria exist between levels I and II in the form of electron transport and between levels III and IV in the form of ionic transport, but that no equilibrium exists between levels II and III, representing the interface of reference redox couple 14 and ion selective membrane 20, and resulting in a "blocked" interface. As described above, such a "blocked" junction potential is typically unstable and irreproducible, resulting in imprecision and inaccuracy in electrochemical analysis. An ion selective sensor 30 in accordance with one embodiment of the present invention is schematically illustrated in cross-section in Fig. 2, typically fabricated atop substantially planar non-conducting substrate 32, and comprises reference redox couple 34, polymeric material 40 in contact therewith, and ion selective material 42 in contact with polymeric material 40. Substrate 32 may comprise any electrically insulating material such as glass, ceramic, silicon wafer, plastic, polymer resin or the like, the particular substrate material or its configuration not being critical to the present invention. Redox couple 34 is typically deposited atop a portion of substrate 32 and may comprise any standard redox reference couple, for example a metal 36 and a salt of the metal 38. In a preferred embodiment, redox couple 34 comprises a layer of silver 36 with a layer of silver chloride 38 in contact therewith, typically created or deposited thereover. Silver chloride layer 38 may be made according to any known method, for example by printing using standard microfabrication techniques, or by plating from solution, for example from a concentrated solution of potassium chloride or sodium chloride. Lead 39 provides electrical contact for couple 34, and may pass through substrate 32 (as illustrated) or may be deposited upon substrate 32 (not shown). Lead 39 may be made from any conductive material such as silver, copper, nickel, gold, platinum, zinc, etc., and typically comprises silver, platinum, or gold according to preferred embodiments of the present invention. Contacting redox couple 34, and completely covering redox couple 34 and extending onto portions 35 of substrate 32 according to preferred embodiments of the present invention is polymeric material 40. Material 40 may be provided upon redox couple 34 and substrate 32 according to any of the well-known methods for depositing polymeric materials onto other materials, for example by casting from solution as a dissolved polymer or copolymer, polymerizing or copolymerizing the material directly upon the redox couple and substrate, or fabricating a sheet of material 40 and pressing it onto redox couple 34 and substrate 32. According to preferred embodiments of the present invention, polymeric material 40 is cast from solution, either by spin-casting or drop-casting onto redox couple 34 and substrate 32. The solution employed may be any solution in which polymeric material 40 is soluble, typically an organic solvent. Polymeric material 40 may comprise any material having sufficient molecular weight to form a film or coating on redox couple 34 and substrate 32, yet have a molecular weight low enough to be non-crystalline in character, typically in the range of 2,000 to 250,000 Daltons, more typically in the range of 5,000 to 150,000 Daltons. Preferably, polymeric material 40, when contacted with water, relatively quickly and reproducibly equilibrates to a stable swell value. Material 40 should swell so as to comprise a weight not more than 5 times its dry weight when contacted with water, preferably from about 1.5 to about 3 times its dry weight, and more preferably does not swell to more than about 2 times its dry weight when contacted with water. As noted above, rapid and stable equilibration of the swell value of a material involved in electronic or ionic conductivity of an ion selective sensor or other electrochemical device results in rapid and stable equilibration of the overall electrode in terms of precision and accuracy in readout. According to one embodiment of the present invention, polymeric material 40 comprises less than about 1.63 X 10 21 immobilized charged sites per gram (corresponding to less than about 2.72 milliequivalents/gram (meq/g)). As used herein, charged sites per gram and meg/g refer to dry weight of polymeric material 40. Preferably, material 40 comprises from about 5.5 X 10 19 to about 1.4 X 10 21 immobilized charged sites per gram (from about 0.09 to about 2.26 meq/g), more preferably from about 4.1 X 10 20 to about 1.1 X 10 21 immobilized charged sites per gram (from about 0.68 to about 1.81 meq/g), and most preferably from about 5.5 X 10 20 to about 8.2 X 10 20 immobilized charged sites per gram (from about 0.91 to about 1.36 meq/g). Employment of material 40 including these preferred ranges of the number of immobilized charged sites/gram advantageously affects the overall performance of ion selective sensor 30, especially in terms of swell, adherence, longevity, and precision and accuracy. According to another embodiment of the present invention, polymeric material 40 has immobilized sites of charge opposite that of mobile ions involved in redox couple 34. That is, if a typical silver/silver chloride redox couple is employed as a reference 34, polymeric material 40 advantageously includes immobilized positively charged sites, counter to the chloride ions involved in the redox couple. Such a choice of charged polymeric material results in stable equilibrium between reference redox couple 34 and polymeric material 40, as will be further described below. Polymeric material 40 may comprise the polymerization or copolymerization product of at least one monomer carrying at least one charged site, and at least one inert monomer. Preferably, material 40 comprises the polymerization product of cationic, or zwitterionic species, and typically at least one other non-ionic species. A non-limiting exemplary list of charged sites which may be associated with species polymerized to form material 40 includes sulfonate, carboxylate, phosphonate, ammonium groups, quaternary ammonium groups, phosphonium groups, quaternary phosphonium groups, etc. The ions participating in the reference redox couple are selected as counter ions. An exemplary list of polymers suitable for use as material 40 includes polystyrene having fixed charged sites, perfluorinated ionomers, sulfonated styrene-divinyl benzene resins, divinyl naphthalene acid polymers, vinyl pyridinium salts, quaternized vinyl benzyl halides, acrylate polymers such as those described in EP-A-0 625 704 nitrile-containing polymers, and amide-containing polymers. A particularly preferred class of monomers suitable for polymerization or copolymerization to form polymeric material 40 of the present invention is described in U.S. Patent No. 4,434,249, and an article entitled "Acrylic Ion-Transfer Polymers", issued February 28, 1984, by C.L. Ballestrasse and T.R. Beck, Journal of the Electrochemical Society, 134, 11, 2745-2749 (1987). According to one preferred embodiment, polymeric material 40 comprises the copolymerization product of at least one charged acrylic monomer and at least one neutral acrylic monomer. Preferably, the charged acrylic monomer or monomers employed has the formula: where R 1 is selected from the group consisting of hydrogen, hydrocarbon groups, and alcohol groups, and Y has the formula: where R 2 is selected from the group consisting of straight or branched saturated hydrocarbon chains, straight or branched unsaturated hydrocarbon chains and straight or branched saturated or unsaturated hydrocarbon chains having hydroxy functionalities, R 3 , R 4 , and R 5 are each selected from the group consisting of hydrogen, hydrocarbon groups, and alcohol groups, and can be the same or different, and Z - is selected from the group consisting of halides, acetate, and methylsulfate ion. More preferably, R 1 is selected from the group consisting of H and CH 3 , R 2 is selected from the group consisting of straight and branched saturated hydrocarbon chains, R 3 , R 4 , and R 5 are each selected from the group consisting of H and CH 3 and can be the same or different, and Z - is a halide. According to a particularly preferred embodiment, R 1 , R 3 , R 4 and R 5 each comprise CH 3 , R 2 is (CH 2 ) 3 , and Z - is chloride. The neutral acrylic monomer or monomers employed, according to this embodiment, may comprise at least one component of the formula CH 2 =C(R 1 )(COOR 2 ), where R 1 and R 2 are each selected from the group consisting of hydrogen, hydrocarbons, and alcohols, and can be the same or different. Preferably, R 1 is selected from the group consisting of hydrogen and lower alkyl groups, and R 2 is selected from the group consisting of linear, branched and cyclic hydrocarbons and alcohols of from 1 to 20 carbon atoms. According to the above description, hydrocarbon groups such as hydrogen, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, alkaryl, aralkyl may be selected. As used herein, the terms "hydrocarbon", "alkyl", "cycloalkyl" and similar hydrocarbon terminology is meant to include alcohols and hydrogen, although specific reference to the inclusion of hydrogen and/or alcohols is frequently made herein. Examples of such groups are methyl, propenyl, ethynyl, cyclohexyl, phenyl, tolyl, benzyl, hydroxyethyl. Copolymerization of material 40 may be effected by conventional means including anionic, cationic, or free-radical polymerization initiators. In a particularly preferred embodiment, polymeric material 40 comprises a copolymer of methacrylamidopropyltrimethylammoniumchloride (MAPTAC) and methylmethacrylate (MMA). A random copolymer may be employed, for example made from the polymerization reaction of a mixture of these monomers in a predetermined ratio, or a block copolymer comprising blocks of from about 1 to 500 monomer units of each of the above-noted monomers may be fabricated. A block copolymer may be a random mixture of blocks of a variety of molecular weights, or may be a mixture of blocks of relatively narrow molecular weights, depending upon the application. Preferably, a mixture of MAPTAC and MMA monomers are polymerized in solution. According to one of the embodiments of the invention described above, the ratio of relative amounts of MAPTAC and MMA monomers are selected so as to provide the above-described preferred ranges of charged sites/gram (meq/g). To formulate a polymeric material carrying less than about 1.63 X 10 21 immobilized charged sites per gram, a mixture would be polymerized comprising a weight ratio of MAPTAC to MMA of less than about 60/40. To formulate a polymeric material including from about 5.5 X 10 19 to 1.4 X 10 21 immobilized charged sites per gram, a MAPTAC/MMA weight ratio of from about 2/98 to about 50/50 would be copolymerized. To formulate a polymeric material including from about 4.1 X 10 20 to about 1.1 X 10 21 immobilized charged sites per gram, a MAPTAC/MMA weight ratio of from about 15/85 to about 40/60 would be employed. To formulate a polymeric material including from about 5.5 X 10 20 to about 8.2 X 10 20 immobilized charged sites per gram, a MAPTAC/MMA weight ratio of from about 20/80 to about 30/70 would be employed. According to embodiments in which only positively-charged immobilized sites exist in polymeric material 40, addition of salts to material 40 may be particularly advantageous and is within the scope of the present invention. As noted above, the counterions of the immobilized charged sites associated with material 40 are selected so as to be the same as either analyte ions in a solution or ions involved in reference redox couple 34. Salts selected for addition to polymeric material 40 may also be advantageously selected so as to include analyte ions and/or ions involved in reference redox couple 34. For example, when a silver/silver chloride redox couple 34 is employed, ion selective membrane is selective for a particular cation, and polymeric material 40 includes immobilized positively charged sites, a salt including the cation to be analyzed and chloride may advantageously be added to polymeric material 40. Addition of such salts to polymeric material 40 typically advantageously affects the transference characteristic of material 40. The principle transference is described in U.S. Patent No. 4,434,249, referenced above. It is advantageous according to the present invention to fabricate ion selective sensor 30 to have an overall transference approaching an ideal value of 1.0 for the ion to be sensed, while having a transference approaching an ideal value of zero for ions of charge opposite that of the ion to be sensed. However, within polymeric material 40 itself, it is desirable that transference numbers for both cationic and anionic species be greater than zero, preferably between about 0.1 and about 1.0. Addition of salts to polymeric material 40 may be carried out according to several methods. According to one method, polymeric material 40 may be cast as a free-standing polymer, cut to size, and soaked in an aqueous solution comprising the salt to be added. Typically, such an aqueous solution has a concentration of about 0.1-0.2 M. Alternatively, material 40 may be polymerized or copolymerized in the presence of such salts, or may be drop cast or spin cast from a solution including the selected salt during the fabrication of ion sensitive sensor 30 described below. According to another method, salts may be screen-printed onto redox couple 34 prior to application of polymeric material 40. According to this embodiment, a particular salt is added preferably such that the cationic and anionic transference numbers of polymeric material 40 are both within about two orders of magnitude. More preferably, a particular salt is added such that the ratio of cationic to anionic or anionic to cationic transference is not more than about 6.0, still more preferably not more than about 2.6, and most preferably not more than about 1.9. According to preferred embodiments, polymeric material 40 is selected such that such salts may be added without affecting the specificity of cationic or anionic transport within the material. Contacting, and completely covering polymeric material 40 according to preferred embodiments of the present invention is ion selective material 42 selective for potassium, calcium, hydrogen, sodium, or lithium ions. The choice of material 42 is not critical to the present invention, thus selection may be made from any of a wide variety of known materials incorporating a variety of known ionophores or ion exchangers to impart ion selectivity to the material. Ion selective material 42 may be a commercially-available or pre-fabricated membrane cut to size and placed atop polymeric material 40, may be fabricated and dissolved in a suitable solvent and cast onto polymeric material 40, or may be formulated and polymerized in solution atop polymeric material 40. Preferably, ion selective material 42 is a membrane cast from solution atop material 40. Additionally, it is within the scope of the present invention to use other ion selective materials such as ion selective glasses as ion selective material 42. A non-limiting exemplary list of materials suitable for formation of ion selective material 42 includes polyvinylchloride, polystyrene, polyacrylate, polycarbonates, silicone rubber, polyesters, polyamides, vinylidene chloride, acrylonitrile, polyurethanes, polyvinylidene chloride, polyvinylidene chloride copolymerized with polyvinylchloride, polyvinyl butyryl, polyvinyl formal, polyvinyl acetate, polyvinyl alcohol, cellulose esters, and copolymers of the above materials, as well as glasses. Plasticizers may be used in the preparation of a membrane comprising ion selective material 42, such as o-nitrophenyl-octyl ether, dimethylphthalate, dioctylphenyl-phosphonate, dibutylphthalate, hexamethylphosphoramide, dibutyladipate, dioctylphthalate, diundecylphthalate, dioctyladipate, dioctyl sebacate, and other conventional plasticizers. As noted, to impart ion selectivity to material 42, a suitable ionophore or ion exchanger is typically employed. Any known ionophore selective to the ion to be analyzed may be employed. A non-limiting exemplary list of ionophores includes: for potassium, valinomycin, dicyclohexano-18-crown-6, dibenzo-18-crown-6, tetraphenyl borate, tetrakis (p-chlorophenyl) borate; for calcium, bis(didecylphosphate), bis(4-octylphenylphosphate), bis(4-(1, 1,3,3-tetramethylbutyl)phenylphosphate tetracosamethylcyclododecasiloxane, N, N'-di(11-ethoxycarbonyl) undecyl)-N, N',4, 5-tetramethyl-3,6-dioxaoctane diamide; for hydrogen, tridodecylamine, N-methyl N-octadecyl (1-methyl, 2-hydroxy, 2-phenyl) ethylamine, N-octadecyl 3-hydroxy n-propylamine, N, N' bis s (octadecyl ethylene amine), p-octadecyloxy-m-chlorophenylhydrazonemeso oxalonitrile; for sodium, monensin, N,N',N''-triheptyl-N, N', N"-trimethyl-4,4', 4"-propylidintris-(3-oxabutyramide), N,N,N',N'-tetracyclohexyl-1,2-phenylenedioxydiacetamide, 4-octadecanoyloxymethyl-N,N,N',N',-tetracyclohexyl-1,2-phenylenedioxydiacetamide, bis[(12-crown-4)methyl]dodecylmethylmalonate; for lithium, N, N'-diheptyl-N, N', 5,5-tetramethyl-3,7-dioxononanediamide), 12-crown-4, 6,6-dibenzyl-14 crown-4. A variety of components and methods for fabrication of ion selective materials, in particular membranes, in accordance with the present invention are known in the art and may be found, for example, in International Patent Publication No. WO 91/11710, and U.S. Patent Nos. 4,214,968, 3,562,129, 3,753,887, and 3,856,649, as well as EP-A-0 325 562 referenced above. Referring now to the scheme of Fig. 2, an approximation of the advantageous chemical equilibria associated with the ion selective sensor of the present invention is represented. Level V represents electronic flow to and from redox couple 34 through lead 39. Level VI represents the electrochemical equilibrium associated with redox couple 34 such as, for example, silver/silver chloride. Level VII illustrates the association of the ion X - of redox couple 34, for example chloride ion, with portions of polymeric material 40 represented by P 2 , and the incorporation of an ion to be analyzed, for example, a cation represented as A + , associated with portions of polymeric material 40 as represented by P 3 . If immobilized positively-charged sites are associated with polymeric material 40, the association represented by P 2 X - is enhanced when silver/silver halide is selected as redox couple 34, as well as association with any anion to be analyzed. If polymeric material 40 includes immobilized negatively-charged sites, association with any positive ion included in an electrochemical equilibrium associated with redox couple 34 and/or association with a positively charged ion to be analyzed, represented in Fig. 2 as cation A + , is enhanced. If polymeric material 40 is selected so as to comprise only positively-charged or negatively-charged immobilized sites, it is preferably also selected so as to be able to incorporate to some extent ions of a charge the same as that of the immobilized sites, so that equilibrium both with anions associated with redox couple 34 and cations associated with the analyte species may exist (as described above), and this may ensue according to the preferred ranges of immobilized charged sites per gram of polymeric material 40 according to the present invention. Level VIII of the scheme of Fig. 2 represents portions of ion selective material 42, represented as P 1 , associated with the ion to be analyzed, cation A + in this scheme. Level IX represents the analyte medium containing exemplary analyte A + , which may comprise an aqueous or organic solution, blood or plasma, skin, or the like, a wide variety of analyte media being measurable with ion selective sensors fabricated in accordance with the present invention. As can be seen from the scheme of Fig. 2, equilibria exist between each of the levels V-IX. Between levels V and VI, electronic transport exists, similarly to the state of the prior art represented by levels I and II of Fig. 1. Between levels VIII and IX, ionic transport exists, similarly to the state of transport between levels III and IV in the representation of the prior art in Fig. 1. However, according to the present invention, between levels VI and VII, ionic transport exists, aided by association between portions P 2 of polymeric material 40 and an ion associated with the equilibrium of redox couple 34 (X - ). Additionally, ionic transport between levels VII and VIII exists, in the form of exemplary analyte ion (A + ) transport between portion P 1 of ion selective material 42 (level VIII) and polymeric material 40 (level VII). The result is thus "unblocked" junction potential across ion selective sensor 30, resulting in improved precision and accuracy in analysis of ionic species. As noted above, one problem commonly associated with fabrication of planar electrochemical devices is poor adherence between layers. Often delamination is a determining factor in the lifetime of a particular device, or in the feasibility of device production. The ion selective sensor of the present invention is commonly mounted in a sampling device comprising a sample chamber which is mounted so as to cover ion selective material 42 above redox couple 34, the sample chamber allowing a sample solution to contact material 42 above redox couple 34. An exemplary sample chamber is described in EP-A-0 625 704. referenced above. In such a sampling device, with reference to Fig. 2, a gasket or other apparatus generally applies pressure atop ion selective material 42 in the direction of substrate 32, which may alleviate some delamination problems once device fabrication is complete. However, typical microfabrication of such sensors involves fabrication of a plurality of devices on a single chip, followed by singulation (dicing) of the chip to provide a plurality of sensors, and then installation of each sensor device into an encasing sample device. Such singulation and separation may result in delamination if adherence between the various layers is not good. It has surprisingly been found that polymeric material 40, according to preferred embodiments of the present invention, adheres well to a variety of insulating substrate materials and to a variety of ion selective materials, such that auxiliary binding layers are not needed between polymeric material 40 and substrate 32 or between material 40 and material 42. Mechanical adhesion of layers can be characterized by methods including the tape, blister, scratch/scrape, ultrasonic bath and peel tests. A simple yet effective semi-quantitative test for adherence is the tape test. In a typical procedure, a sensor fabricated in accordance with the present invention, schematically represented in Fig. 2, is fabricated on a chip along with a plurality of such electrodes. A piece of commercially available (3M) adhesive tape is pressed atop a chip including a plurality of such electrodes, typically a chip of about 5 by 5 cm (2 inches by 2 inches) in dimension, and the tape is removed by slowly pulling upwards at an angle approximately perpendicular to the surface of the chip. Tape is advantageously selected to have an adhesive strength such that if mechanical adhesion between the layers is good the tape will peel off without disrupting the layers, but if adhesion is poor delamination will occur. Alternatively, pieces of tape with increasing adhesive properties may be used in such a test until delamination of one layer from another layer occurs, or rupture of any layers occurs. A goal in fabrication of ion selective sensors such as those of the present invention is that, when tape of sufficient adhesive quality is used, rupture of ion selective material 42, especially when material 42 comprises a membrane, and/or polymeric material 40 will occur rather than delamination of ion selective material 42 from polymeric material 40, or delamination of polymeric material 40 from substrate 32. Stated another way, the polymeric material 40 is selected so as to bond sufficiently to substrate 32 and to ion selective material 42 such that adhesion between polymeric material 40 and substrate 32 and between polymeric material 40 and ion selective material 42 is stronger than force needed to rupture either material 42 or material 40. Material selected as polymeric material 40 in accordance with the present invention surprisingly shows good adhesive properties. The result is surprising in that, as noted above, immobilized charged sites associated with polymeric material are thought to be inconsistent with good adhesion of such polymeric material to an insulating substrate or to adjacent layers in typical planar electrochemical devices. The dimensions of ion selective sensor 30 not critical to the present invention. Dimensions typically found in planar electrochemical devices fabricated according to conventional thin-film or thick-film techniques are acceptable. Additionally, although substrate 32 is illustrated in Fig. 2, upon which ion selective sensor 30 is fabricated, sensor 30 may be fabricated without a substrate, in the form of the well-known "dipped" electrode. Such an embodiment will be clearly understood by referring to U.S. Patent No. 3,714,015. In the following examples, a preliminary procedure was used to evaluate the sensors of the present invention. This preliminary procedure described is not meant to constitute a final, rigorous evaluation. The following examples are intended to illustrate the benefits of the present invention, but do not exemplify the full scope of the invention. For example, although the thick-film technique is exclusively exemplified, it is to be understood that the thin-film technique may be selected; although only a one-electrode device is fabricated, a device including a plurality of electrodes on a single chip could be fabricated, as well as a plurality of transducers on a single chip. Additionally, the specific shape and arrangement of the components of the electrode of the present invention may be significantly altered, such alteration being within the scope of the invention. These and other modifications and their equivalents are understood to be within the scope of the present invention. EXAMPLE 1 In this and the following examples, ion selective sensors were fabricated by screen printing a plurality of individual electrodes on a laser scored ceramic wafer, and following the deposition of an ion selective membrane, the wafer was singulated on the laser score lines so as to create a plurality of individual sensor chips. For the purpose of simplicity in this and the following examples, procedures will be described as if a single chip were fabricated. An ion selective sensor base chip was fabricated on a .457 cm x 1.143 cm electrically insulating composite substrate compromising approximately 96% Al 2 O 3 and approximately 4% binder, available from Coors Ceramic Company, Grand Junction, Colorado. The laser score process needed for wafer singulation is available from Lasereliance Technologies, Altamonte Springs, Florida. Using the thick-film deposition technique, a conductive strip was fabricated by screen printing, using a framed, stainless 325 mesh/.01 mm emulsion-coated screen available from Affiliated Manufacturers, Inc., North Branch, New Jersey. The silver conductive paste is available as part no. 3571 UF, from Metech Company of Elverson, Pennsylvania. The conductive strip was fabricated so as to create an oval electrode with the approximate dimensions of 1.52 mm x .762 mm. The paste was fired using a Fast Fire, 7 zone belt furnace with an attached 3 zone dryer available from BTU of Billerica, Massachusetts, in accordance with manufacturer's recommendations. Subsequently, a gold conductor and contact pad was screen printed so as to overlap and make contact to the silver conductor. The contact pad extends approximately 2.03 mm from the Dielectric coating edge and has a contact area of approximately 1.66 mm. The gold paste is available as part no. MTPC10391 from Metech Company, Elverson, Pennsylvania. Firing was carried out according to manufacturer's recommendations. A dielectric (glass) passivation was then printed over both conductors with openings so as to define the active electrode area and the contact pads. The dielectric paste, part no. 9615, is available from E.I. Dupont, Wilmington, Delaware, and was fired according to manufacturer's recommendations. The gold contact pads were masked with 0.63 cm (.250") skived TFE film tape with a silicon adhesive available from Green Rubber, Cambridge, Massachusetts. The silver electrodes were then galvanostatically plated with silver chloride from 0.1 M KCl for 10 minutes at -2.00 mA. The tape was removed and the chip was rinsed in deionized water and air dried. EXAMPLE 2 A copolymer of MAPTAC and MMA was synthesized according to the following method. MAPTAC was purchased as a 50 weight percent aqueous solution inhibited with 600 ppm MEHQ from Aldrich of Milwaukee, Wisconsin, and was used as received. MMA was purchased from Aldrich of Milwaukee, Wisconsin, and was distilled prior to use. Isopropyl alcohol (IPA) was HPLC grade from Fisher of Pittsburgh, Pennsylvania, and was used as received. Anhydrous ethanol was from Quantum Chemical of Cincinnati, Ohio, and was used as received. Azobisisobutyronitrile (AIBN) was from Kodak Chemical of Rochester, New York, and was recrystallized in acetone prior to use. Anhydrous diethyl ether was from Fisher, and was used as received. A copolymer having a weight ratio of 25 parts MAPTAC to 75 parts MMA was synthesized as follows. 10 mL of IPA, 5 g of a 50 weight percent aqueous solution of MAPTAC and 7.5 g of MMA were added to a test tube which was then covered with a septum. A needle connected to a nitrogen line was inserted into the septum and the reaction mixture was mixed with nitrogen bubbles for about 5 minutes. 0.11 g of AIBN was next added to the reaction mixture and this was mixed for an additional 20 minutes with nitrogen bubbles. The needle was removed and the test tube was placed in a 70°C water bath for 2.5 hours. The water bath was then removed and the test tube sat capped overnight at room temperature. The polymer was removed from the test tube by breaking the glass. Pieces of polymer were dissolved in a 10% solution of anhydrous ethanol, precipitated into anhydrous diethyl ether, filtered, and then dried 30 minutes with vacuum. EXAMPLE 3 Silated PVC was synthesized in house, according to EP-A-555952 A 25/75 weight ratio of MAPTAC/MMA, prepared according to Example 2, was dissolved as a 5% weight solution in ethanol. A chip fabricated according to Example 1 was prepared as described in Example 1, and the ethanol solution containing MAPTAC/MMA was drop cast thereover using a Pasteur pipette. The ethanol was driven off by drying at room temperature followed by drying at 80°C for 30 minutes. The resultant MAPTAC/MMA layer had a thickness of about 10 mm. The chip was then spun cast with a 1% weight solution of silated PVC in tetrahydrofuran at 4,000 RPM for 30 seconds and cured for 2 hours at 80°C. The resultant silated PVC layer had a thickness of about 1 mm. EXAMPLE 4 A chip including a membrane selective for hydrogen ion (a pH sensor) was fabricated as follows. The pH sensor was prepared by depositing a hydrogen ion selective membrane atop the sensor fabricated in accordance with Example 3 according to the following method. Tetrahydrofuran (THF) was purchased from Aldrich, of Milwaukee, Wisconsin. Tridodecylamine (TDDA) was purchased from Fluka, of Buchs, Switzerland. Potassium tetrakis (p-chlorophenyl) borate (KTpClPB) was purchased from Fluka. Dioctylphthalate (DOP) was purchased from Fluka. PVC was purchased from Fluka. A 10% by weight membrane solution was prepared in THF containing 2 weight percent TDDA, 0.1 weight percent KTpClPB, 65 weight percent DOP, and 33 weight percent PVC. A volume of 3.6 ml of membrane solution was solvent cast onto a chip fabricated in accordance with Example 3. The layer was dried at room temperature in a THF environment for about 24 hours. Final membrane thickness was approximately 120 mm. EXAMPLE 5 A chip including a membrane selective for the potassium ion was fabricated as follows. Valinomycin (VAL) was purchased from Fluka. Diundecylphthalate (DUP) was purchased from Scientific Polymer Products of Ontario, New York. A 10% by weight membrane solution was formulated in THF containing 1 weight percent VAL, 33 weight percent PVC, 66 weight percent DUP, and 0.2 weight percent KTpClPB. A membrane layer was cast atop a chip fabricated in accordance with Example 3 in the manner described in Exhibit 4. EXAMPLE 6 A chip including a membrane selective for the sodium ion was fabricated as follows. Methyl monensin ester (MMO) was purchased from Calbiochem of LaJolla, California. o-nitrophenol octyl ether (NPOE) was purchased from Fluka. A 10% by weight membrane solution was formulated in THF containing 2 weight percent MMO, 30 weight percent PVC, 67.6 weight percent o-NPOE, and 0.4 weight percent KTpClPB. A membrane layer was cast atop a chip fabricated in accordance with Example 3 in the manner described in Example 4. EXAMPLE 7 A chip including a membrane selective for the calcium ion was fabricated as follows: (R,R)-N,N'-[BIS(11-ethoxycarbonyl)undecyl]-N,N'-4,5-tetramethyl-3,6-doxaoctane diamide (ETH1001) was purchased from Fluka. A 10 percent by weight solution in THF was prepared by adding 3.3 weight percent ETH1001, 1.2 weight percent KTpClPB, 30 weight percent PVC, and 6.5.5 weight percent NPOE. The solution was solvent cast onto a chip prepared in accordance with Example 3 in the manner described in Example 4. EXAMPLE 8 Five day whole blood and serum studies were conducted for pH sensors using chips fabricated in accordance with Example 4. Sample chambers were constructed so as to expose all sample solutions to an area of the ion selective membrane immediately above the reference redox couple. A conventional silver/silver chloride reference electrode and the gold contact pad of the pH chip were connected to a high impedance voltmeter, the reference electrode also being exposed to sample solutions. Seven sensors were tested. The sensors were first wetted in pH 7 buffer and initial slopes were determined. The sensors were then soaked for approximately 48 hours in the buffer solution. On day one, potentiometric selectivity coefficients were determined using the fixed interference method. Buffer solutions were: 1) 10 mM NaOH, 130 mM NaCl, 10 mM TRIS, 2) 190 mM KCl, 10 mM KOH, 10 mM TRIS, 3) 60 mM LiOH, 6.6 mM citric acid, 11.4 mM boric acid, 4) 130 mM CaCl 2 , 20 mM Ca(OH) 2 , 10 mM TRIS, and 5) 130 mM MgCl 2 , 20 mM Mg(OH) 2 , 10 mM TRIS. The pH of each solution was adjusted by dropwise addition of 1 N HCl. Slope was determined at the end of the day. On days 2-4, the following test sequence was carried out: (A) aqueous test (slope determination and triplicate measurements of a variety of pH standard solutions); (B) the pH of 20 samples of human serum was measured; (C) aqueous test, as in (A); (D) pH measurement of 10 human whole blood samples, followed by a slope determination (WB 1); (E) a repeat of step (D) for a second blood sample (WB 2); (F) a repeat of step (D) for a third blood sample (WB 3); (G) a repeat of the aqueous test of step (A). The results of this test are given in Table 1. The average readings of each of the seven sensors are displayed along with standard deviation and % cv, measured against the results of a control pH test run on the same samples using a commercially available pH sensor (Ciba Corning Diagnostics Corp., 200 series glass pH electrode). The results show good precision and accuracy of pH measurement carried out in accordance with the ion selective pH sensor of the present invention. Selectivity of the pH sensor of the present invention, with respect to lithium, sodium, potassium, magnesium, and calcium were determined using the fixed interference method. Selectivity, slope, and linearity of the sensor was good. EXAMPLE 9 The five (5) day whole blood and serum study of Example 8 was carried out using potassium sensors using chips fabricated in accordance with Example 5. Four potassium sensors were fabricated. On day 1, potentiometric selectivity coefficients were determined using the separate solution method. Results were similar to conventional K + electrodes. On days 2-4, the test sequence described in Example 8 was carried out, with the exception that step A was carried out using 644 Cal and 644 Slope solutions, commercially available from Ciba Corning Diagnostics of Medfield, Massachusetts and potassium was measured rather than pH. The results of this test are given in Tables 2 and 3. The average readings of each of the four sensors are displayed along with standard deviation and % CV, measured against the results of a control potassium test run on the same samples using a commercially available potassium sensor (Ciba Corning Diagnostics Corp. 200 series potassium electrode). The accuracy and precision of the blood and serum feasibility test was very good. Slope, linearity, and selectivity coefficients were also good. EXAMPLE 10 The five day whole blood and serum study described in Example 8 was conducted for sodium sensors using chips fabricated in accordance with Example 6. Sample chambers were constructed as in Example 8. The slope and calibration solutions described in Example 9 were used. The control sensor was a commercially available sodium sensor (Ciba Corning Diagnostics Corp. 200 series glass sodium sensor). Table 4 gives average precision values for 5 sensors fabricated according to this example. The results are very good. Slope, linearity, and selectivity were also good. EXAMPLE 11 The five day whole blood and serum study described in Example 8 was conducted for calcium sensors including chips fabricated in accordance with Example 7. Five sensors were fabricated. Sample chambers were constructed in accordance with Example 8. The slope and calibration solutions were 634 cal and 634 slope solutions, commercially available from Ciba Corning Diagnostics Corp. Table 5 lists average precision values. Precision and accuracy are very good. Linearity, slope and selectivity were also good. EXAMPLE 12 Transference number determinations in the MAPTAC/MMA membrane material fabricated in accordance with Example 2, were carried out. Free-standing MAPTAC/MMA was formed by drop casting from a 5 weight percent solution in ethanol, similar to the drop casting method described in Example 3. The free-standing membranes, after air-drying, had a thickness of approximately 82 mm. The membranes were soaked in 160 mM solution of NaCl for about 30 minutes, and swelled to about 2.1 times their dry weight as a result. Circular sections were cut out of the free-standing membranes and mounted in the well-known Phillips bodies. The fill solution was the same as the soak solution and a silver/silver chloride internal reference was used. EMF measurements were made in beakers with a saturated KCl calomel reference electrode. Transference numbers were determined by the EMF method whereby membrane potentials are measured using electrolyte concentrations C1 and C2 on either side of the membrane. The concentration of NaCl on one side was kept constant at 160 mM and the concentration C2 of NaCl or KNO 3 on the other side was varied. Reference to this well-known method may be found in "Transport Phenomena in Membranes", by N. Lakshminarayanaiah, New York, Academic Press, (1969). Results are tabulated in Table 6. Appreciable cationic as well as anionic transport in the films tested was observed. Ionic transport was also observed to be a non-selective phenomenon, as evidenced by the similarity in the results when NaCl is replaced by KNO 3 . EXAMPLE 13 A pH sensor was prepared in accordance with Example 4. A 25/75 weight ratio of MAPTAC/MMA in ethanol was spun cast on the chip for 30 seconds at 750 RPM. The chip was air dried. A pH membrane was cast atop the chip in accordance with Example 4. Using 6200C Permanent Mending Tape from 3M Corporation of St. Paul, Minnesota, the tape was pressed atop the chip and slowly removed by pulling upwards at an angle approximately perpendicular to the surface of the chip. Adhesion was observed to be good. Aqueous performance was tested over 40 days and was very good. K+, SERUM SERUM mM CONCENTRATION PRECISION %CV SENSOR # DAY 2 DAY 3 DAY 4 DAY 2 DAY 3 DAY 4 1 4.45 4.34 4.29 1.80 0.22 0.27 2 4.58 4.33 4.34 0.83 0.26 0.30 3 4.58 4.36 4.31 0.97 0.20 0.18 4 4.43 4.35 4.34 0.87 0.14 0.10 CONTROL 4.38 4.33 4.33 0.52 0.40 0.34 K+, WHOLE BLOOD SENSOR NO. 1 2 3 4 CONTROL DAY 2 4.40 4.34 4.36 4.34 4.33 0.03 0.04 0.03 0.03 0.01 0.77 0.81 0.80 0.68 0.28 4.29 4.20 4.23 4.21 4.23 0.03 0.04 0.03 0.03 0.02 0.69 0.85 0.62 0.62 0.46 4.24 4.17 4.20 4.21 4.16 0.02 0.02 0.03 0.02 0.02 0.53 0.47 0.61 0.46 0.42 DAY 3 4.15 4.04 4.09 4.10 4.01 0.03 0.04 0.04 0.04 0.01 0.74 1.00 0.94 0.88 0.31 4.15 4.06 4.12 4.10 4.11 0.03 0.03 0.03 0.03 0.02 0.67 0.69 0.68 0.67 0.45 3.72 3.65 3.68 3.68 3.57 0.03 0.03 0.03 0.03 0.01 0.70 0.85 0.81 0.87 0.26 DAY 4 4.18 4.11 4.26 4.16 4.12 0.05 0.04 0.06 0.04 0.00 1.11 1.08 1.39 0.96 0.08 4.03 4.01 4.00 4.03 4.00 0.03 0.03 0.08 0.03 0.00 0.65 0.65 1.88 0.75 0.10 3.82 3.79 3.83 3.80 3.81 0.03 0.02 0.03 0.02 0.01 0.76 0.60 0.77 0.61 0.38 Na+ SENSOR PRECISION WHOLE BLOOD SERUM +/- 1.4% +/- 0.45% 1.6 0.40 1.3 0.95 1.1 0.58 1.5 0.38 Ca++ SENSOR PRECISION WHOLE BLOOD SERUM +/- 1.6% +/- 1.6% 1.7 2.1 1.9 0.8 1.9 2.3 2.7 1.3 TRANSFERENCE NUMBER MEASUREMENTS C 2 range slope r 2 t + t - 0.12 - 0.20 M NaCl 41.9 0.984 0.35 0.65 0.12 - 0.20 M KNO 3 27.0 0.940 0.23 0.77 10 -5 - 1 M NaCl 33.5 0.983 0.28 0.72 slope = Slope of Cell EMF r 2 = Correlation Coefficient t + = Cation Transference Number t - = Anion Transference Number

Claims: An ion selective sensor (30) comprising: an electrically conductive material providing a reference redox couple (34) formed from a metal and a salt thereof, the salt including first and second ions, the first ions being ions of the metal having a first charge and the second ions having a second charge opposite the first charge; and an ion selective material (42) selective for potassium, calcium, hydrogen, sodium, or lithium ions, covering an intermediate layer of a polymeric material; characterised in that the polymeric material (40) provided on the said electrically conductive material includes third and fourth ions, the third ions being immobilized on the polymeric material, the fourth ions being mobile and being the same as the second ions. A sensor as claimed in claim 1 wherein the said polymeric material includes less than 1.63 x 10 21 immobilized charge sites per gram, preferably from about 5.5 x 10 19 to about 1.4 x 10 21 immobilized charged sites per gram, more preferably from about 4.1 x 10 20 to about 1.1 x 10 21 immobilized charged sites per gram, most preferably from about 5.5 x 10 20 to about 8.2 x 10 20 immobilized charged sites per gram. A sensor as claimed in any of claims 1 or 2 wherein the said polymeric material includes immobilized positively-charged sites and immobilized negatively-charged sites. A sensor as claimed in any of claims 1 to 3 wherein it further comprises a non-electrically conducting substrate (32), the said redox couple being provided on the said substrate and the said polymeric material being provided so as to cover the said redox couple and to extend onto the said substrate, preferably the said polymeric material being selected so as to adhere firmly to the said substrate and to the said ion selective material and to form bonds thereto which are stronger than the force required to rupture the said ion selective material or the said polymeric material. A sensor as claimed in any of claims 1 to 4 wherein the said polymeric material swells to a weight of not more than 5 times its dry weight when contacted with water, preferably to a weight of from about 1.5 to about 3 times its dry weight when contacted with water, more preferably to a weight of about 2 times its dry weight when contacted with water. A sensor as claimed in any of claims 1 to 5 wherein the said polymeric material comprises the copolymerization product of at least one charged monomer and at least one member selected from neutral monomers and polymers. A sensor as claimed in claim 6 wherein the said polymeric material comprises the copolymerization product of at least one charged acrylic monomer and at least one neutral acrylic monomer. A sensor as claimed in claim 7 wherein the said at least one neutral acrylic monomer comprises at least one component corresponding to the following general formula: CH 2 =C(R 1 )(COOR 2 ), wherein R 1 and R 2 are independently selected from hydrogen, hydrocarbons and alcohols; preferably R 1 is selected from hydrogen and lower alkyl groups and R 2 is selected from linear, branched and cyclic hydrocarbons and alcohols having from 1 to 20 carbon atoms; more preferably the said neutral acrylic monomer comprises methylmethacrylate. A sensor as claimed in claim 7 wherein the said at least one charged acrylic monomer corresponds to the following general formula: wherein R 1 is selected from hydrogen, hydrocarbons and alcohol; and Y corresponds to the following general formula: wherein R 2 is selected from straight or branched saturated hydrocarbons, straight or branched unsaturated hydrocarbons and straight or branched saturated or unsaturated hydrocarbons having hydroxy functionalities; R 3 , R 4 and R 5 are independently selected from hydrogen, hydrocarbons and alcohols; and Z - is selected from halide, acetate and methylsulfate ions; preferably R 1 is selected from H and CH 3 ; R 2 is selected from straight and branched saturated hydrocarbons; R 3 , R 4 and R 5 are independently selected from H and CH 3 ; and Z - is a halide; more preferably R 3 , R 4 and R 5 are each CH 3 ; and Z - is chloride; most preferably the said at least one charged acrylic monomer comprises methacrylamidopropyltrimethylammoniumchloride. A sensor as claimed in any of claims 1 to 9 wherein the said electrically conductive reference electrode material providing a redox couple comprises a conductive metal, silver, and a salt of the said conductive metal, silver chloride, in contact therewith. A sensor as claimed in any of claims 1 to 10 wherein it further comprises a salt added to the said polymeric material. A sensor as claimed in any of claims 1 to 11 wherein the said polymeric material has a ratio of anionic to cationic or cationic to anionic transference numbers of less than about 6.0, preferably less than about 2.6, more preferably less than about 1.9. A method of providing a stable and reproducible electrical interface between a solid contact reference providing a redox couple formed from a metal and a salt thereof, the salt including first and second ions, the first ions being ions of the metal having a first charge and the second ions having a second charge opposite the first charge and an ion selective material of an ion selective sensor characterised in that it comprises: contacting both the said solid contact reference and the said ion selective material with a polymeric material including third and fourth ions, the third ions being immobilised on the polymeric material, the fourth ions being mobile and being the same as the second ions. A method as claimed in claim 13 wherein the said polymeric material is as defined in any of claims 2, 3 or 5 to 7. A method as claimed in claim 13 or claim 14 wherein the said solid contact reference is provided on a substrate and the said polymeric material covers the said solid contact reference and extends to cover a portion of the said substrate, the said polymeric material being selected so as to adhere firmly to the said substrate. A method as claimed in any of claims 13 to 15 wherein the said solid contact reference comprises a conductive metal, silver, and a salt of the said conductive metal, silver chloride, in contact therewith. A method of forming an ion selective sensor comprising the steps of: providing an electrically conductive material; creating a redox couple formed from a metal and a salt thereof, the salt including first and second ions, the first ions being ions of the metal having a first charge and the second ions having a second charge opposite the first charge including a portion of the said electrically conductive material; coating the said redox couple with a polymeric material including third and fourth ions, the third ions being immobilised on the polymeric material, the fourth ions being mobile and being the same as the second ions; and covering the said polymeric material with an ion selective material selective for potassium, calcium, hydrogen, sodium, or lithium ions; and, optionally, selecting an electrically non-conductive substrate; and depositing the said electrically conductive material onto a portion of the said substrate. A method as claimed in claim 17 wherein the said coating step comprises casting a reaction mixture, dissolved in an organic solvent, including a polymerization product as defined in any of claims 7 to 9 onto the said salt layer so as completely to cover the said layer with the said mixture; and drying the said mixture of the said organic solvent.

Inventors: CHAN ANDY D C, CHAN, ANDY D.C.
Applicants: BAYER AG, BAYER CORPORATION
Application year: 1994
Main classification: G01N27
IPC codes: C08L101, C08F220, C08F20, G01N27